|Publication number||US4552154 A|
|Application number||US 06/588,277|
|Publication date||Nov 12, 1985|
|Filing date||Mar 12, 1984|
|Priority date||Mar 12, 1984|
|Publication number||06588277, 588277, US 4552154 A, US 4552154A, US-A-4552154, US4552154 A, US4552154A|
|Inventors||Jerome T. Hartlaub|
|Original Assignee||Medtronic, Inc.|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (5), Referenced by (92), Classifications (8), Legal Events (4)|
|External Links: USPTO, USPTO Assignment, Espacenet|
1. Field of the Invention
This invention relates to implanted medical devices and, more particularly relates to a physiological waveform morphology discriminator and method for use in a pacemaker for characterizing the origin of cardiac depolarizations.
2. Description of the Prior Art
A variety of disease mechanisms may result in cardiac dysrhythmias. Typically these dysrhythmias are characterized by electrical instability in the cardiac tissue which results in abnormal mechanical activity of the heart. The abnormal mechanical activity results in the reduction of the rate at which oxygenated blood is circulated throughout the body. The parameter is called cardiac output. If the loss of cardiac output results from a heartbeat slower than a normal heartbeat responding to the same physiologic demand, the dysrhythmia is called a bradycardia. In contrast, an abnormally rapid beating of the heart which also results in reduced cardiac output is generically termed a pathologic tachycardia.
Pacers for the treatment of bradycardia are known from U.S. Pat. No. 3,478,746 to Greatbatch. This patent teaches a demand type (VVI) pacemaker which provides a stimulus to cardiac tissue through a pacing lead; if no naturally occurring cardiac activity is sensed within a preset time period referred to as the escape interval. Consequently, the stimulating pulses are supplied to the heart only when the intrinsic heart rate drops below a preset minimum corresponding to this escape interval.
The intrinsic heart rate is detected by a demand pacer through a sense amplifier. A sense amplifier typically provides passband amplification at the frequencies which predominate in the intracardiac signal as obtained from the left ventricle. The amplification stage is typically followed by a level detection stage which provides a logic level output if the input physiological waveform meets both passband and amplitude criteria. Examples of sense amplifiers as used in demand pacers include the device taught by U.S. Pat. No. 3,927,677 to Gobeli.
More recent pacers have been proposed for the treatment of tachycardia. Both U.S. Pat. Nos. 3,698,398 and 3,693,627 to Berkovits teach the use of a pacer therapy to treat a tachyarrhythmia. Like a demand pacer, the tachy treatment pacer utilizes a sense amplifier to detect the cardiac depolarizations. Typically the tachyarrhythmia treatment therapy is invoked when the rate of cardiac depolarizations as measured by the sense amplifier reach a preset limit between 120 beats per minute and 200 beats per minute. There are two problems associated with the use of a simple rate detection system for the detection of a pathologic tachyarrhythmia. One problem is that pathologic tachyarrhythmias can have rates within the range shared by normal heart activity. There is, in effect, an overlap between the physiologically normal heart rate which does not require treatment and the pathologic heart rate which does require therapy.
An additional problem relates to the detection by the pacer system of beats of ectopic or abnormal origin. A normal heat beating at a physiologically normal rate may be interrupted by occasional premature ventricular contractions (PVC). These PVC's appear on the EKG interspersed among sinus beats in the patient's electrocardiogram. Consequently, a rate detection algorithm operating on sensed depolarizations detected by a sense amplifier could interpret a PVC as a tachyarrhythmia.
The PVC as well as other beats of abnormal origin differ in their shape or morphology from a normally conducted sinus beat. Typically, for example, the amplitudes and durations associated with PVC's are larger than those associated with normal beats and the slope or rise time of the signal is somewhat less than the intrinsic deflection of a normally conducted R-wave. These time domain differences in the signal do not produce substantial changes in the frequency spectra of the signal. As a consequence, conventional sense amplifiers relying on frequency domain parameters such as bandpass amplification are incapable of distinguishing normally conducted R-waves from abnormal beats despite the differences in their time domain morphology.
The ability to distinguish between ectopic beats and sinus beats would aid immeasurably in the formulation of pacer therapies for cardiac dysrhythmias in general, and tachyarrhythmias in particular.
FIG. 1 is a functional block diagram of an implantable pacer incorporating the present invention.
FIG. 2 is a collection of waveforms depicting the operation of the system.
FIG. 3 is a flow chart describing the operation of the invention.
The waveform morphology detector of the present invention includes apparatus and method for producing a numerical index dependent upon the time domain characteristics of the waveform associated with the cardiac depolarization. The value of the numerical index is compared with a reference value to determine whether the candidate waveform has a waveform shape similar to the reference value to assist in providing the correct therapy.
The reference value may be entered into the device through a non-invasive programming system or may be developed by the implanted device based upon a historical average of waveforms associated with normally conducted cardiac depolarizations.
The structure for carrying out the invention includes a counter which is enabled by the output of a one shot. The one shot is initiated by the output of a conventional sense amplifier which detects cardiac activity. After a sensed cardiac depolarization, the counter begins to accumulate counts generated by a voltage controlled oscillator (VCO). The VCO in turn is controlled by the output voltage of a preamplifier. The preamplifier generates an output voltage corresponding to the instantaneous value of the cardiac depolarization. As a consequence, the number in the counter at the end of a preset timing interval reflects the shape of the cardiac depolarization. The timing means for generating the preselected timing interval may be remotely programmed or may be fixed.
Turning to FIG. 1 there is shown a functional block diagram of a pacer incorporating the present invention. The pacemaker designated generally as 10 is connected to the cardiac tissue through a lead system 12 having a sensing electrode 14 and a stimulating electrode 16.
The pacing function is achieved through software control of a microprocessor system generally designated 18. This system includes a central processing unit (CPU) and volatile (RAM) as well as non-volatile (ROM) memory. The software driven microprocessor system 18 communicates to additional pacer logic through an I/O port 20 which interfaces the pacer with an output amplifier 22 which provides the therapeutic stimulation to the cardiac tissue.
A telemetry system 24 is provided which permits the non-invasive programming of pacing parameters as well as telemetry of information acquired by the implanted device. This pacing system also includes a sense amplifier 23 for detecting the depolarization of cardiac tissue and communicating this information to the CPU. The pacing system may be configured to operate in any of the known pacing modalities including ventricular demand pacing mode (VVI), atrio-ventricular sequential pacing mode (DVI), atrial-synchronized, ventricularly inhibited pacing mode (VDD), dual demand pacing mode (DDD), and tachyarrhythmia pacing modes.
The waveform discriminator apparatus is most useful when the pacemaker operates in a tachyarrhythmia detection and treatment mode. In a tachyarrhythmia treatment mode it is useful to distinguish the origin of sensed cardiac depolarizations since the efficacy of a stimulation or treatment regime depends strongly upon the source and mechanism of a tachyarrhythmia. Conventional rate discrimination arrhythmia detection systems are incapable of accurately characterizing the origin of the arrhythmia and may, in some instances, invoke a therapeutic treatment regime when such treatment is inappropriate. When used in conjunction with the tachyarrhythmia pacer it is anticipated that the waveform morphology discriminator will be one detection criteria which will be satisfied prior to the initiation of a tachyarrhythmia treatment.
Prior art tachyarrthmia treatment devices including that taught by U.S. Pat. No. 3,693,627 to Berkovits operates under VVI mode generating an output stimulus at the end of an external control and delivers a burst of closely paced stimuli through an output amplifier to the cardiac tissue in an effort to disrupt or break up the tachyarrhythmia.
The pacemaker as shown in FIG. 1 may operate in a conventional demand (VVI) mode wherein the sense amplifier 23 will reset a software implemented escape interval timer within the CPU through the I/O port 20. If the sense amplifier does not detect a cardiac depolarization within the preset escape interval an output stimulus will be issued from the output amplifier 22 by a control signal provided to the output amplifier through the I/O port 20.
If the rate of cardiac depolarizations exceeds a preset limit, then a tachyarrhythmia treatment will not be invoked unless the origin and/or nature of the cardiac depolarization is an abnormal one. Traditional sense amplifiers have been unable to determine the origin and nature of cardiac depolarizations since they operate only on the frequency domain characteristics of the intercardiac signal.
By contrast, the physiological waveform discriminator of the present invention relies upon the time domain characteristics or morphology of the input waveform to ascertain its origin and/or nature. In operation, after a cardiac depolarization is initially sensed the sense amplifier 24 will issue an interrupt signal to the microprocessor based pacing system 18 which will enable the voltage controlled oscillator 26 and counter 28. The sense amplifier will also initiate the operation of one-shot 32. The intercardiac waveform present at electrode 14 will be amplified in preamplifier 30 which will modulate a voltage controlled oscillator 26 delivering a bit rate to the clock input of counter 28. The counter 28 will be enabled for a preset time period after the sense amplifier has detected the intracardiac waveform. The count within the counter 28 at the end of the preset time will be transferred through the I/O port 20 to the microprocessor system 18. After the contents of the counter have been read it will be reset by a control signal developed by the microprocessor unit 18 and delivered to the counter 28 through the I/O port 20. Although a discrete counter is shown in FIG. 1, it should be appreciated that a counter could be implemented in software. The number transferred from the counter 28 to the microprocessor system 18 may be compared with a reference value stored in memory. If the value of the counter departs significantly from a characteristic value stored in memory the beat may be considered of abnormal origin and/or nature.
The waveform diagram of FIG. 2 clarifies the operation of the invention. Waveform A is on intracardiac electrocardiogram from a patient indicating the R-wave complexes 1-5 associated with a cardiac depolarization. Waveform complex 4 shown in Waveform A is a premature ventricular contraction (PVC) which is typically characterized by large amplitude and relatively slow slew rate excursions about the base line. Waveform B is the output of sense amplifier 24 in response to the intercardiac electrocardiogram of Waveform A. Note that shortly after the onset of the R-wave, the sense amplifier produces a logic 1 output level. This state transition initiates the operation of the one-shot 32 which enables the counter for the time-out period associated with the one-shot function.
The area under the sense amplifier output pulses in the voltage versus time plot of FIG. 2 may be a predefined function of the sense amplifier filtering that is employed. Such filtering can be adjusted for preferential sensing of different sensed signals, and multiplexed or switched filters could be advantageously utilized for this purpose.
The preamplifier 30 monitors the cardiac waveform available at terminal 14 and generates an output voltage proportional to the instantaneous value of the cardiac waveform. This voltage is supplied to the voltage controlled oscillator which produces a bit-rate dependent upon the value of the output voltage of the preamplifier. This system converts the instantaneous amplitude of the intracardiac electrocardiogram to a frequency rate supplied to counter 28. The output of the VCO is shown as Waveform D in FIG. 2.
In the FIG. 3 the value of the counter is displayed with respect to time. The counter value is zero at the start of the counting sequence. The counting sequence is initiated by the depolarization of cardiac tissue and the counts accumulate on the counter for the preset time interval. At the end of the time interval the value of the counter is read. Note that the premature ventricular contraction (PVC) results in a count higher than those for the normally conducted sinus beats.
The count associated with exemplar PVC shown by complex 4 deviates from the representative count associated with the normal complexes 1, 2, 3 and 5 of Waveform A. This deviation is calculated by the microprocessor system 18. It is anticipated that a representative count number or reference value will be stored in memory and this value will be compared with the count associated with a candidate waveform. If the count of the candidate waveform is substantially higher or lower than the reference value, the beat will be classified as a non-sinus beat. The difference between the reference count and the candidate count may be non-invasively programmed to set a count window criteria shown on FIG. 4. Alternatively, the count window and reference value may be developed by the system based on a run of sinus beats.
For example, the count associated with a sequence of normally conducted sinus beats may be averaged to determine the index count. The upper and lower bounds of the count window may be taken as the highest count associated with a normally conducted complex, while the lower bound may be taken as the lowest count associated with a normally conducted beat.
The selection of the reference count and count window may be performed after the pacer is implanted. If a number of non-sinus or abnormal beats are detected within a preset time window a tachyarrhythmia treatment stimulation regime may be entered by the pacer. The occurrence of abnormal beats may be stored at specified memory locations and the value stored may be accessed by the attending physician through the telemetry system.
Although a specific embodiement of the invention has been described, it will be apparent to those skilled in the art that the scope of the present invention is intended to extend to dual chamber and atrial only applications as well as ventricular applications and for both pacing as well as tachycardia control and defibrillation systems.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3144019 *||Aug 8, 1960||Aug 11, 1964||Edgar Haber||Cardiac monitoring device|
|US3524442 *||Dec 1, 1967||Aug 18, 1970||Hewlett Packard Co||Arrhythmia detector and method|
|US3658055 *||Apr 11, 1969||Apr 25, 1972||Hitachi Ltd||Automatic arrhythmia diagnosing system|
|US3829766 *||Apr 2, 1973||Aug 13, 1974||Hellige & Co Gmbh F||Electrocardiogram monitoring apparatus|
|US4388927 *||Dec 13, 1979||Jun 21, 1983||American Hospital Supply Corporation||Programmable digital cardiac pacer|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US4721114 *||Feb 21, 1986||Jan 26, 1988||Cardiac Pacemakers, Inc.||Method of detecting P-waves in ECG recordings|
|US4830006 *||Jun 17, 1986||May 16, 1989||Intermedics, Inc.||Implantable cardiac stimulator for detection and treatment of ventricular arrhythmias|
|US5050599 *||May 17, 1990||Sep 24, 1991||Siemens Aktiengesellschaft||Implantable medical device for detecting events occurring with respect to a physiological function with variable sensitivity and a method for the operation of such a device|
|US5086772 *||Jul 30, 1990||Feb 11, 1992||Telectronics Pacing Systems, Inc.||Arrhythmia control system employing arrhythmia recognition algorithm|
|US5097832 *||Mar 9, 1990||Mar 24, 1992||Siemens-Pacesetter, Inc.||System and method for preventing false pacemaker pvc response|
|US5193536 *||Dec 20, 1990||Mar 16, 1993||Medtronic, Inc.||Paced cardioversion|
|US5240009 *||Mar 25, 1991||Aug 31, 1993||Ventritex, Inc.||Medical device with morphology discrimination|
|US5261401 *||Nov 3, 1989||Nov 16, 1993||James Baker||Ambulatory cardiac diagnostic units having means for inhibiting pacemaker response|
|US5301677 *||Feb 6, 1992||Apr 12, 1994||Cardiac Pacemakers, Inc.||Arrhythmia detector using delta modulated turning point morphology of the ECG wave|
|US5313953 *||Jan 14, 1992||May 24, 1994||Incontrol, Inc.||Implantable cardiac patient monitor|
|US5411529 *||Sep 13, 1993||May 2, 1995||Medtronic, Inc.||Waveform discriminator for cardiac stimulation devices|
|US5447523 *||Jul 22, 1994||Sep 5, 1995||Biotronik Mess-Und Therapiegerate Gmbh & Co.||Pacemaker with physiological control of stimulation|
|US5507783 *||Jan 11, 1995||Apr 16, 1996||Pacesetter, Inc.||Pacemaker mediated tachycardia response for VDD and VDDR modalities|
|US5513644 *||Sep 22, 1994||May 7, 1996||Pacesetter, Inc.||Cardiac arrhythmia detection system for an implantable stimulation device|
|US5560369 *||Sep 22, 1994||Oct 1, 1996||Pacesetter, Inc.||Cardiac arrhythmia detection system for an implantable stimulation device and method|
|US5620471 *||Jun 16, 1995||Apr 15, 1997||Pacesetter, Inc.||System and method for discriminating between atrial and ventricular arrhythmias and for applying cardiac therapy therefor|
|US5623936 *||Dec 5, 1995||Apr 29, 1997||Pacesetter, Inc.||Implantable medical device having means for discriminating between true R-waves and ventricular fibrillation|
|US5782881 *||Sep 20, 1996||Jul 21, 1998||Lu; Richard||Pacemaker with safety pacing|
|US5788717 *||Jul 11, 1995||Aug 4, 1998||Pacesetter, Inc.||Atrial rate determination and atrial tachycardia detection in a dual-chamber implantable pacemaker|
|US5817134 *||Feb 25, 1997||Oct 6, 1998||Greenhut; Saul E.||Apparatus and method for detecting atrial fibrillation by morphological analysis|
|US6128527 *||Dec 3, 1997||Oct 3, 2000||University Of Iowa Research Foundation||Apparatus and method of analyzing electrical brain activity|
|US6934649 *||May 15, 2001||Aug 23, 2005||Synchro Kabushiki Kaisha||Waveform detection system and state-monitoring system|
|US7103405||Aug 29, 2003||Sep 5, 2006||Medtronic, Inc.||Methods and apparatus for discriminating polymorphic tachyarrhythmias from monomorphic tachyarrhythmias facilitating detection of fibrillation|
|US7130677||Aug 29, 2003||Oct 31, 2006||Medtronic, Inc.||Methods and apparatus for discriminating polymorphic tachyarrhythmias from monomorphic tachyarrhythmias facilitating detection of fibrillation|
|US7242978||Dec 2, 2004||Jul 10, 2007||Medtronic, Inc.||Method and apparatus for generating a template for arrhythmia detection and electrogram morphology classification|
|US7496409||Mar 29, 2006||Feb 24, 2009||Medtronic, Inc.||Implantable medical device system and method with signal quality monitoring and response|
|US7774064||Aug 10, 2010||Cardiac Pacemakers, Inc.||Cardiac response classification using retriggerable classification windows|
|US7826893||Nov 2, 2010||Medtronic, Inc.||Method and apparatus for generating a template for arrhythmia detection and electrogram morphology classification|
|US7937148||May 3, 2011||Nanostim, Inc.||Rate responsive leadless cardiac pacemaker|
|US7945333||Oct 13, 2006||May 17, 2011||Nanostim, Inc.||Programmer for biostimulator system|
|US7953476||Feb 16, 2006||May 31, 2011||Cardiac Pacemakers, Inc.||Discrimination of supraventricular tachycardia and ventricular tachycardia events|
|US7991457||Aug 2, 2011||Cardiac Pacemakers, Inc.||Discrimination of supraventricular tachycardia and ventricular tachycardia events|
|US8010209||Aug 30, 2011||Nanostim, Inc.||Delivery system for implantable biostimulator|
|US8145310||Jul 7, 2008||Mar 27, 2012||Cardiac Pacemakers, Inc.||Non-captured intrinsic discrimination in cardiac pacing response classification|
|US8185202||May 22, 2008||May 22, 2012||Cardiac Pacemakers, Inc.||Implantable cardiac device for reduced phrenic nerve stimulation|
|US8209013||Sep 14, 2006||Jun 26, 2012||Cardiac Pacemakers, Inc.||Therapeutic electrical stimulation that avoids undesirable activation|
|US8229552||Jul 24, 2012||Cardiac Pacemakers, Inc.||Discrimination of supraventricular tachycardia and ventricular tachycardia events|
|US8260421||May 22, 2008||Sep 4, 2012||Cardiac Pacemakers, Inc.||Method for reducing phrenic nerve stimulation|
|US8265736||Aug 7, 2007||Sep 11, 2012||Cardiac Pacemakers, Inc.||Method and apparatus to perform electrode combination selection|
|US8295939||Oct 23, 2012||Nanostim, Inc.||Programmer for biostimulator system|
|US8332022||Sep 25, 2006||Dec 11, 2012||Medtronic, Inc.||Methods and apparatus for discriminating polymorphic tachyarrhythmias from monomorphic tachyarrhythmias facilitating detection of fibrillation|
|US8352025||Oct 13, 2006||Jan 8, 2013||Nanostim, Inc.||Leadless cardiac pacemaker triggered by conductive communication|
|US8457728||May 9, 2011||Jun 4, 2013||Medtronic, Inc.||Automatic detection of premature ventricular complexes for heart rate turbulence measurements|
|US8457742||Oct 13, 2006||Jun 4, 2013||Nanostim, Inc.||Leadless cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator|
|US8521284||Dec 12, 2003||Aug 27, 2013||Cardiac Pacemakers, Inc.||Cardiac response classification using multisite sensing and pacing|
|US8527068||Feb 2, 2010||Sep 3, 2013||Nanostim, Inc.||Leadless cardiac pacemaker with secondary fixation capability|
|US8543205||Oct 12, 2011||Sep 24, 2013||Nanostim, Inc.||Temperature sensor for a leadless cardiac pacemaker|
|US8606357||Dec 22, 2008||Dec 10, 2013||Cardiac Pacemakers, Inc.||Cardiac waveform template creation, maintenance and use|
|US8615297||Aug 27, 2012||Dec 24, 2013||Cardiac Pacemakers, Inc.||Method and apparatus to perform electrode combination selection|
|US8615310||Dec 13, 2011||Dec 24, 2013||Pacesetter, Inc.||Delivery catheter systems and methods|
|US8649866||Feb 10, 2009||Feb 11, 2014||Cardiac Pacemakers, Inc.||Method and apparatus for phrenic stimulation detection|
|US8788035||Dec 7, 2012||Jul 22, 2014||Pacesetter, Inc.||Leadless cardiac pacemaker triggered by conductive communication|
|US8788053||Oct 17, 2012||Jul 22, 2014||Pacesetter, Inc.||Programmer for biostimulator system|
|US8798745||Apr 19, 2013||Aug 5, 2014||Pacesetter, Inc.||Leadless cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator|
|US8831726||Jan 15, 2008||Sep 9, 2014||Cardiac Pacemakers, Inc.||Cardiac response classification using multiple classification windows|
|US8843199||Aug 26, 2013||Sep 23, 2014||Cardiac Pacemakers, Inc.||Cardiac response classification using multisite sensing and pacing|
|US8855789||Jul 26, 2011||Oct 7, 2014||Pacesetter, Inc.||Implantable biostimulator delivery system|
|US8983602||Nov 20, 2013||Mar 17, 2015||Cardiac Pacemakers, Inc.||Method and apparatus to perform electrode combination selection|
|US8996112||Jan 17, 2014||Mar 31, 2015||Cardiac Pacemakers, Inc.||Method and apparatus for phrenic stimulation detection|
|US9008771||Mar 5, 2012||Apr 14, 2015||Cardiac Pacemakers, Inc.||Non-captured intrinsic discrimination in cardiac pacing response classification|
|US9008775||Mar 13, 2014||Apr 14, 2015||Cardiac Pacemakers, Inc.||Method and apparatus to perform electrode combination selection|
|US9020611||Oct 12, 2011||Apr 28, 2015||Pacesetter, Inc.||Leadless cardiac pacemaker with anti-unscrewing feature|
|US9037239||Jul 24, 2008||May 19, 2015||Cardiac Pacemakers, Inc.||Method and apparatus to perform electrode combination selection|
|US9060692||May 23, 2013||Jun 23, 2015||Pacesetter, Inc.||Temperature sensor for a leadless cardiac pacemaker|
|US9072913||Apr 29, 2011||Jul 7, 2015||Pacesetter, Inc.||Rate responsive leadless cardiac pacemaker|
|US9095265||Nov 20, 2013||Aug 4, 2015||Cardiac Pacemakers, Inc.||Cardiac waveform template creation, maintenance and use|
|US9126032||Dec 13, 2011||Sep 8, 2015||Pacesetter, Inc.||Pacemaker retrieval systems and methods|
|US9168383||Oct 19, 2011||Oct 27, 2015||Pacesetter, Inc.||Leadless cardiac pacemaker with conducted communication|
|US9192774||Jun 27, 2014||Nov 24, 2015||Pacesetter, Inc.||Cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator|
|US9216298||Oct 13, 2006||Dec 22, 2015||Pacesetter, Inc.||Leadless cardiac pacemaker system with conductive communication|
|US9227077||Nov 23, 2010||Jan 5, 2016||Pacesetter, Inc.||Leadless cardiac pacemaker triggered by conductive communication|
|US9242102||Dec 20, 2011||Jan 26, 2016||Pacesetter, Inc.||Leadless pacemaker with radial fixation mechanism|
|US9272155||Aug 14, 2013||Mar 1, 2016||Pacesetter, Inc.||Leadless cardiac pacemaker with secondary fixation capability|
|US9308375||Sep 5, 2014||Apr 12, 2016||Cardiac Pacemakers, Inc.||Cardiac response classification using multisite sensing and pacing|
|US9352160||Mar 23, 2015||May 31, 2016||Cardiac Pacemakers, Inc.||Method and apparatus for phrenic stimulation detection|
|US9358400||Oct 13, 2006||Jun 7, 2016||Pacesetter, Inc.||Leadless cardiac pacemaker|
|US20040059760 *||May 15, 2001||Mar 25, 2004||Youichi Ageishi||Waveform detector and state monitoring system using it|
|US20040111120 *||Aug 29, 2003||Jun 10, 2004||Shantanu Sarkar|
|US20040111121 *||Aug 29, 2003||Jun 10, 2004||Brown Mark L.|
|US20050137485 *||Dec 2, 2004||Jun 23, 2005||Jian Cao||Method and apparatus for generating a template for arrhythmia detection and electrogram morphology classification|
|US20060122527 *||Feb 16, 2006||Jun 8, 2006||Cardiac Pacemakers, Inc.||Discrimination of supraventricular tachycardia and ventricular tachycardia events|
|US20060247693 *||Apr 28, 2005||Nov 2, 2006||Yanting Dong||Non-captured intrinsic discrimination in cardiac pacing response classification|
|US20070016257 *||Sep 25, 2006||Jan 18, 2007||Brown Mark L|
|US20070239220 *||Mar 29, 2006||Oct 11, 2007||Greenhut Saul E||Implantable medical device system and method with signal quality monitoring and response|
|US20070276276 *||Jun 4, 2007||Nov 29, 2007||Jian Cao|
|US20110034817 *||Oct 11, 2010||Feb 10, 2011||Marcovecchio Alan F||Discrimination of supraventricular tachycardia and ventricular tachycardia events|
|EP0310216A2 *||Jun 10, 1988||Apr 5, 1989||Chinese Pla General Hospital||Apparatus for detecting heart characteristics using electrical stimulation|
|EP0399059A1 *||May 22, 1989||Nov 28, 1990||Pacesetter AB||Implantable medical device with adjustable sensitivity to detect an event relating to a physiological function, and process for using same|
|EP0469817A2 *||Jul 29, 1991||Feb 5, 1992||Telectronics N.V.||Arrhythmia control system employing arrhythmia recognition algorithm|
|EP0601775A2 *||Dec 1, 1993||Jun 15, 1994||Pacesetter, Inc.||Cardiac event detection in implantable medical devices|
|EP0778050A2||Dec 4, 1996||Jun 11, 1997||Pacesetter Inc.||Implantable medical device having cardiac event detection system|
|WO1990004942A1 *||Nov 3, 1989||May 17, 1990||James Baker||Ambulatory cardiac diagnostic units|
|U.S. Classification||600/515, 607/14|
|International Classification||A61N1/362, A61B5/0468|
|Cooperative Classification||A61N1/3621, A61B5/0468|
|European Classification||A61N1/362A, A61B5/0468|
|Mar 12, 1984||AS||Assignment|
Owner name: MEDTRONIC, INC., 3055 OLD HIGHWAY EIGHT, P.O. BOX
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST.;ASSIGNOR:HARTLAUB, JEROME T.;REEL/FRAME:004239/0497
Effective date: 19840308
|Apr 11, 1989||FPAY||Fee payment|
Year of fee payment: 4
|Apr 16, 1993||FPAY||Fee payment|
Year of fee payment: 8
|Apr 23, 1997||FPAY||Fee payment|
Year of fee payment: 12